Porous biocompatible polymer material and methods

ABSTRACT

Embodiments described include devices and methods for forming a porous polymer material. Devices disclosed and formed using the methods described a spacer for spinal fusion, craniomaxillofacial (CMF) structures, and other structures for tissue implants.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation application of U.S. application Ser.No. 15/066,195, filed on Mar. 10, 2016, which is a divisionalapplication of U.S. patent application Ser. No. 13/967,422, filed Aug.15, 2013, which is a continuation of U.S. patent application Ser. No.12/666,216, filed Oct. 20, 2010, which is a 371 U.S. National Phase ofInternational Patent Application No. PCT/US2009/000604, filed Jan. 30,2009, which claims the benefit of U.S. Provisional Application No.61/025,426, filed on Feb. 1, 2008, the contents of which areincorporated by reference in their entireties herein.

TECHNICAL FIELD

The present structures and methods relate to porous polymer materialsand methods for making porous polymer materials and structures. Examplestructures include, but are not limited to, spacers for spinal fusion,Craniomaxillofacial (CMF) structures, other materials and structures forbone replacement.

BACKGROUND

Spinal fusion is a common technique used to treat chronic back paincaused by degenerated or herniated disk. The technique involves theremoval of a disc between two vertebrae and replacing it with anintervertebral spacer. The intervertebral spacer maintains spacingbetween the two vertebrae and preferably results in fusion through thespacer. The intervertebral spacers may be constructed of autogenic bonetissue taken from a patient's own bone. Allogenic spacers areconstructed of bone harvested from donors. Artificial spacers arecurrently the most common spacer type and may be constructed of metallicmaterial such as titanium or stainless steel or polymers such aspolyetheretherketone (PEEK).

PEEK has recently become popular due to its biocompatibility, andnaturally radiotranslucent characteristics, resulting in limitedinterference with x-ray and CT imaging. However, while PEEK isbiocompatible, bone treats it as a foreign body during the remodelingprocess and isolates it with a fibrous tissue capsule. This fibroustissue prevents direct bony apposition and adhesion to the implant.Other materials, such as titanium, allow for direct bony apposition andongrowth, hut they are typically not radiotranslucent and it becomesdifficult to assess the fusion formation.

Other areas where PEEK is used as an orthopedic biomaterial experiencesimilar fibrous encapsulation. Such indications include custom machinedbodies that are used to fill defects in the skull and cranium. WithPEEK, MRI and CT imaging is generally easier as compared to titanium,but the implant is never fully incorporated into the bone and softtissue does not adhere to the implant.

Ceramic materials such as calcium phosphates, β-TCP, hydroxyapatites andthe like allow for direct bony apposition much like titanium. However,they are typically limited in their strength and toughness. Therefore,it is desirable to construct a material that combines more of thedesired properties from other individual materials described above, suchas toughness and strength, less interference with MRI, X-ray or CTimaging, tissue adhesion, etc.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

The foregoing summary, as well as the following detailed description ofpreferred embodiments of the invention, will be better understood whenread in conjunction with the appended drawings. For the purposes ofillustrating the polymeric porous bodies for promotingingrowth/throughgrowth of the present application, there is shown in thedrawings preferred embodiments. It should be understood, however, thatthe application is not limited to the precise arrangements andinstrumentalities shown. In the drawings:

FIG. 1A illustrates a top view of a porous biocompatible materialaccording to an embodiment of the invention.

FIG. 1B illustrates a top view of a porous biocompatible materialaccording to the prior art.

FIG. 2 illustrates a top plan view of PEEK granules with β-TCP on thesurface according to an embodiment of the invention.

FIG. 3 illustrates a top perspective view of a porous spacer with athrough hole according to an embodiment of the invention.

FIGS. 4A, 4B, and 4C illustrate a front plan view, a front sectionalperspective view, and a front exploded view, respectively, of a spacerhaving a solid core according to an embodiment of the invention.

FIGS. 5A, 5B, and 5C illustrate a front plan view, a front perspectivesectional view, and a front perspective exploded view of a spacer havinga solid band according to an embodiment of the invention.

FIGS. 6A, 6B, and 6C illustrate a top perspective view, a frontperspective view, and a top perspective exploded view of another spacerwith a solid portion according to an embodiment of the invention.

FIGS. 7A, 7B, and 7C illustrate a front perspective sectional view, aside perspective exploded view, and a front perspective view of anotherspacer according to an embodiment of the invention.

FIG. 8 illustrates a front perspective view of a total disc replacementimplant for disc arthroplasty according to an embodiment of theinvention.

FIGS. 9A, 9B, and 9C illustrate a front perspective view, a top planview, and a side perspective view of a spacer and a fixation plateaccording to an embodiment of the invention.

FIG. 10 illustrates a side perspective view and a side perspectivesectional view of a spacer including an instrument engagement featureaccording to an embodiment of the invention.

FIG. 11 illustrates a perspective view and a side view of a lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 12 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 13 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 14 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 15 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 16 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 17 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 18 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 19 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 20 illustrates a perspective view and a side view of another lumbarspinal spacer including a porous material according to an embodiment ofthe invention.

FIG. 21 illustrates a perspective view of a cervical spinal spacerincluding a porous material according to an embodiment of the invention.

FIG. 22 illustrates a perspective view of another cervical spinal spacerincluding a porous material according to an embodiment of the invention.

FIG. 23 illustrates a perspective view of another cervical spinal spacerincluding a porous material according to an embodiment of the invention.

FIG. 24 illustrates a front perspective view of a porous lumbar spaceraccording to an embodiment of the invention.

FIGS. 25A and 25B illustrate a side plan view and a top plan view,respectively, of a porous spacer according to an embodiment of theinvention.

FIG. 26 illustrates a graph showing the relationship between thecompressive strength and the porosity of the spacer of FIG. 24 .

FIG. 27 illustrates a graph showing the relationship between thecompressive strength of the spacer of FIG. 25A-25B.

FIGS. 28A and 28B illustrate a front perspective views of samplestructures with solid cores according to an embodiment of the invention.

FIG. 29 illustrates a graph showing the differences between thecompressive moduli (stiffnesses) of various structures according to anembodiment of the invention.

FIG. 30 illustrates a graph showing the ultimate compressive strengthsof various structures according to an embodiment of the invention.

DETAILED DESCRIPTION OF THE INVENTION

Numerous embodiments are described in this patent application, and arepresented for illustrative purposes only. The described embodiments arenot, and are not intended to be, limiting in any sense. The presentlydisclosed invention(s) are widely applicable to numerous embodiments, asis readily apparent from the disclosure. One of ordinary skill in theart will recognize that the disclosed invention(s) may be practiced withvarious modifications and alterations, such as structural and chemicalmodifications. Although particular features of the disclosedinvention(s) may be described with reference to one or more particularembodiments and/or drawings, it should be understood that such featuresare not limited to usage in the one or more particular embodiments ordrawings with reference to which they are described, unless expresslyspecified otherwise.

The present disclosure is neither a literal description of allembodiments nor a listing of features of the invention that must bepresent in all embodiments.

Neither the Title (set forth at the beginning of the first page of thispatent application) nor the Abstract (set forth at the end of thispatent application) is to be taken as limiting in any way as the scopeof the disclosed invention(s).

In reference to FIG. 1 and FIG. 2 , there is illustrated the differencein final structure between a PEEK/β-TCP, tricalcium phosphate, mixtureand a PEEK-only material placed in a 400° C. furnace for 5 minutes.Specifically, FIG. 1 shows PEEK granules that may be utilized toconstruct a porous spacer according to embodiments described in moredetail below. The granules of the first preferred embodiment include aPEEK/beta-TCP mixture, having particles within a size range of 0.5-1.0mm, with TCP applied at 400 degrees Centigrade for 5 minutes.

Inventive subject matter described herein relates to porous or partiallyporous body composites used to manufacture devices such as spacers forspinal fusion and tissue ingrowth surfaces in orthopedic devices, and tomethods for making and using the porous bodies.

In one embodiment, a method is shown for making a porous intervertebralspacer usable in spinal fusion. The porous intervertebral spacersdescribed herein include a main body made partially or totally of acomposite. In selected embodiments, a main body includespolyetheretherketone, particles and a surface coating of beta tricalciumphosphate (β-TCP) covering at least a portion of the PEEK particles.Although PEEK is a polymer used in one example the invention is not solimited. Other embodiments utilize various thermoplastics other than orin addition to PEEK or combinations of polymers.

Porous spacer embodiments provide an initial stability and ultimatelyallow bony ingrowth from an inferior and superior vertebrae. In order tohave good vascularization and bony ingrowth, pore structure of a porousspacer is generally interconnecting. In one example, a mean pore size asmeasured with mercury porosimetry, and is preferably in a range of100-500 μm. The range of 100-500 μm is not intended to be limiting andat least a portion of the pores may fall outside of this range. It isgenerally understood that to allow mammalian tissue ingrowth, the poresmust be large enough to allow a vascular network to be formed which atminimum requires passage of a red cell which is approximately 5-10 μmand thus this defines the desired lower size limit of at least a portionof the pores. A broader range of pores could thus be 5-5000 μm.

In one embodiment, a porous body formed using techniques described inthe present disclosure are further perfused with patients' bone marrowand/or blood. The use of these autologous biologically active substancescan provide a source of cells and growth factors that can accelerate theformation of bone and tissue into and on the porous structure and canalso help to lead the precursor cells to differentiate down the desiredpath (i.e stem cells into osteoblasts that form bone). In oneembodiment, the porous bodies are infused with allogenic biologicalsubstances to impart a similar effect. In selected embodiments,biologically active substances such as growth factors including, but notlimited to BMP II, BMP VII and PDGF are infused. Synthetic smallmolecules that stimulate bone or tissue formation are included in someembodiments. Such small molecules include, but are not limited to,statins. Although individual additive substances are recited above,combinations of substances are also within the scope of the invention.

In some embodiments, the porous structure is modified to retain thesebiologically active substances and release them over an extended periodof time or direct the location of their release and activity. In someembodiments the porous structure is coated with a substance that holdsand then releases an active substance over a desired period. Thematerials used in such a coating include but are not limited tomaterials that hydrolytically degrade such as aliphatic polyesters suchas PLA and PGA and hydrogels such as PEG and CMC. Alternately, in someembodiments the surface of the porous structures or treatments providesthe desired release kinetics. Such surface structures includemicroporosity and changing the surface wettability.

In other embodiments a biologically active substance is applied to aseparate carrier that is applied or inserted into the porous body ofthis invention. In one embodiment, a separate carrier is pre-insertedinto a porous body. In one embodiment, a porous body is modified withareas of at least partially reduced porosity to reduce or prevent therelease of the biologically active substance in certain directions. Inone example, a thin outer shell of a non-porous polymer or othermaterial is placed on a porous core to prevent the release of abiologically active substance in a radial direction. An advantage ofsuch a configuration is realized in cervical fusion where the release ofgrowth factors such as BMP II in a radial direction can lead toundesired tissue growth. In selected embodiments a non-porous materialis made from a resorbable material so that the directionally controlledrelease is time dependant.

In one example method, polymer particles that have a specific particlesize range are mixed with beta tricalcium phosphate (β-TCP), to form amixture of polymer granules and coating powder. In one embodiment, themixing provides an at least partial coating of the β-TCP around thesurface of the polymer particles. Alternate materials that can be usedto coat the polymer include, but are not limited to, calcium powders,bone powder, hydroyapatite, titanium (including titanium alloys andtitanium oxides), barium salts and zirconium oxide. The mixture isplaced in one or more molds at a temperature above a melting point ofthe polymer and held for a time effective to form bonding at the contactpoints of melted polymer particles.

In selected embodiments the powder coating the surface the of thepolymer is subsequently removed and a microporous surface structure isobtained, the microprobes resulting from the volume previously occupiedby the powder coating particles. An effective pore size of thismicroporous structure is in range of 0.1 and 100 microns.

In one example, the β-TCP powder inhibits, slows or in some embodiments,prevents the flow of polymer material above the melt temperature andcauses the polymer particles to bead. An end product is a continuouslyporous material with a specific geometry that generally replicates thegeometry of the mold. Examples of polymer material include, but are notlimited to, PEEK, carbon reinforced PEEK, PEKK, PAEK family, PEK PEKK,PEKEKK, PCL, PLA, PGA, polyphenylene, self-reinforced polyphenylene,polyphenylsulphone, polysulphone, PET, polyethylene, polyurethane orother biocompatible polymers.

In some embodiments, additional materials are incorporated into theporous body. In one embodiment, the polymer particles are fusedthroughout a reinforcing structure. This reinforcing structure could bemade from any known biocompatible material including titanium andstainless steel or the polymer itself and can provide additionalmechanical strength to the porous body. In another embodiment,radiopaque materials are incorporated to provide selective areas ofradiopacity so the location of the body can be visualized with X-rays orCT. These radiopaque materials include, but are not limited to,biocompatible metals (e.g. titanium aluminum nitride (TAN), titaniumaluminum vanadium (TAV), tantalum, gold, barium, titanium, stainlesssteel), barium sulfate; zirconium oxide and radiopaque dyes. In otherembodiments, the radiopaque material is used to mechanically reinforcethe porous structure.

In some embodiments, the porous structure is selectively compressed inselective areas to impart increased mechanical strength. Thiscompression is achieved through a combination of heat and or pressure.Methods to produce this heat and pressure include but are not limited toultrasonics, radio frequency heating, induction heating, lasers ordirect heating. These areas of reinforcement may form features forengagement with an instrument or structural ribs.

Exemplary Embodiments

Porous PEEK Method

One process embodiment creates porous intervertebral spaces. The processembodiment includes using a polymer in particulate form. The particlesize is in a range of 0.25-1.0 mm. This range is not intended to belimiting and other particle sizes can be used. The particles are mixedwith β-TCP at a ratio of 90% polymer 10% β-TCP. The particle size ofβ-TCP is in a range of 0.01-0.1 mm. The particles are placed in acontainer and are mixed thoroughly. This mixing can be performed using astandard lab vortex shaker. The shaking allows the smaller β-TCPparticles to at least partially cover the surface of the polymerparticles. A sieve with a mesh size larger than β-TCP particle size butsmaller than polymer particle size is used to remove the excess β-TCPparticles. The resulting powder mix includes polymer particles coatedwith β-TCP. The purpose of the β-TCP is to prevent the polymer particlesfrom flowing freely when heated above melting point. The presence ofβ-TCP causes the particles to bead and to prevent flow at or above meltpoint of the polymer. This allows for strong bonding between polymerparticles while maintaining the interstitial space. When cooled, thefinal material defines an interconnecting porous polymer with β-TCPcoating. The resulting material has the interconnecting porous structurefor honey ingrowth and a β-TCP coating to produce a calcium rich surfacefor better osteoconduction.

As discussed above, in selected embodiment, the β-TCP or other coatingpowder is later removed from exposed surfaces within pores via an acidleaching, a selective solvent process, or another powder removalprocess. In this case the surface is calcium poor but has a microporousstructure that can be advantageous from a wettability and cellularattachment perspective.

FIGS. 1A and 1B illustrate the difference in final structure between aPEEK/β-TCP mixture and a PEEK-only material placed in a 400° C. furnacefor 5 minutes. FIG. 1A illustrates an interconnecting sample formedusing methods described above with β-TCP on the surface. The particlesize and the amount of the mixed particles inside the mold determine theporosity. The final mold geometry determines the final porous componentsize and shape.

FIG. 1B illustrates a collapsed structure of PEEK particles at the sametemperature and time where no coating particles such as β-TCP were used.As can be seen from the Figures, interstitial spaces are more greatlypreserved when coating particles such as β-TCP are included prior tomelting the mixture. The process embodiments described herein allow forstronger bonding compared to standard sintering methods at quickerprocessing time. Because sintering involves heating the material belowmelt point, the bonding between the particles is not as strong asmaterials bonded by heating the particles to above melting point.

FIG. 2 illustrates PEEK polymer particles coated with β-TCP powder bymixing 90% PEEK and 10% β-TCP by weight prior to melting. The mixturewas placed in a 250 μm sieve to remove the excess β-TCP powder. Theresulting powder consisted of PEEK granules covered with β-TCP powder,as shown in FIG. 2 .

Although a PEEK polymer coated with β-TCP powder is described in theexemplary embodiment above, the invention is not so limited. Otherpolymers coated with other power particles are within the scope of theinvention. One of ordinary skill in the art, having the benefit of thepresent disclosure will recognize that with other polymers and othercoating powders, other processing conditions such as heating temperatureand time, etc, can be adjusted to form porous polymer structures usingalternative materials.

Monolithic Porous Structure

One embodiment of the Porous PEEK structure is a prosthesis forinterverbral body fusion that is made completely of porous PEEK, as isshown in FIGS. 3, 11, and 12A-12B. The prostheses can assume the form ofa variety of external shapes in order to optimize endplate coverage. Thesuperior and inferior surfaces may include pyramidal or unidirectionalteeth or ridges molded in order to increase the devices' primarystability in the intervertebral space. Some embodiments, one of which isas spacer 30 in FIG. 3 , defines one or more axial holes 32 to allowsolid bony through growth. In one embodiment, lateral windows in a side34 of the spacer 30 are further provided to enhance the assessment offusion via radiograph or other suitable techniques. Although a generallycylindrical shape is shown in FIG. 3 as a monolithic porous structureexample, other monolithic porous geometries such as solid cylinders,scaffold shapes, complex molded custom fitted shapes, etc. are withinthe scope of the invention.

Solid Core

FIGS. 4A, 4B and 4C illustrate an implant 40 for intervertebral bodyfusion. The implant 40 is constructed of a solid PEEK core 42 thermallybonded to porous endplates 44. This implant embodiment 40 serves toincrease the ultimate axial compressive strength of the implant whilemaintaining the benefits of bony ingrowth and primary stability.

FIGS. 5A, 5B and 5C illustrate an implant embodiment 50 that includes aporous PEEK main body 52 and a solid band 54, annularly positioned aboutthe main body 52.

Solid Implant Holder

During conventional implantation of an intervertebral body device,desirable that a surgeon maintains precise control of the implant. Oneimportant part of such control is achieved by tightly gripping animplant. It is desirable for the steps of gripping and releasing to besuch that an introduction profile of the spacer is not increased orotherwise changed in any significant way.

In FIGS. 6A, 6B and 6C, an implant holding feature 62 is integrated intoa solid portion 64 of the implant embodiment 60 that is mechanicallyconnected to a porous component 66. An example of a mechanicalconnection includes tabs 63 that fit into corresponding slots. Althoughtabs 63 are shown, other configurations of mechanical connections suchas other interference fit geometries, bayonette fasteners, etc. Theembodiment of FIGS. 6A, 6B and 6C shows the solid portion 64 extendingfrom an inferior to the superior surface of one side 68 of the implantwhich can be positioned to bear the greatest axial loads and to increasea shear strength of the implant by reinforcing the porous component 66.

In the embodiment show, the holding feature 62 includes a pair of slots.In one embodiment a pair of slots such as slots 62 are configured tointerface with a surgeon's tool to provide precise control. One ofordinary skill in the art will recognize that a number of other possibleholding feature configurations such as single slots, protrudingfeatures, etc. are within the scope of the invention.

FIGS. 7A, 7B and 7C, illustrate another example of a holding feature 72.In the example of FIGS. 7A-C, the holding feature 72 is integrated intoa solid core 74 of the implant 70. Similar to embodiments describedabove, the implant 70 is composed of a solid portion 74 which includesthe holding feature 72, and a porous polymer portion 76 formed usingmethods described in embodiments above.

FIG. 10 illustrates another example embodiment 100 including an implantholder feature 102 that is integrated into an exterior geometry of asolid portion 104 which is bonded to a porous body 106. As can be seenfrom the examples, a number of possible configurations for implants andholding features are contemplated.

Porous Endplate Feature on a Device for Disc Arthroplasty

FIG. 8 illustrates one embodiment of an intervertebral prosthesis fordisc arthroplasty at 80 that includes porous PEEK endplates 82 thermallybonded to solid PEEK 84 with lateral insertion slots 86.

Multi-Component Constructs

FIGS. 9A, 9B and 9C illustrates one embodiment of an intervertebralspacer 90 with integrated fixation showing porous PEEK endplates 92thermally bonded to a solid PEEK core 94 and mechanically connected to ametallic plate 96. A central distractor slot aides insertion.

Spinal Spacer Example Configurations

FIGS. 11-20 illustrate a number of example configurations of lumbarspinal spacers including at least a portion of porous polymer materialformed using methods described in the present disclosure. Although anumber of examples are shown, the invention is not so limited. In eachexample, the entire spacer may be formed from porous polymer material asdescribed, or only a portion of the spacer may be formed from porouspolymer material as described. As described herein, other materialconfigurations include a solid portion bonded, mechanically joined, orotherwise attached to a porous portion. Example solid portions includesolid cores, solid bands, solid skins, etc. attached to a porous polymerportion.

FIGS. 21-23 illustrate a number of example configurations of cervicalspinal spacers including at least a portion of porous polymer materialformed using methods described in the present disclosure, Similar todiscussion of lumbar spacers, a number of configurations utilizingporous polymer materials are within the scope of the invention.Configurations that utilize portions of solid material as describedabove are also included.

FIG. 11 shows a spacer 110 that includes at least a portion of porouspolymer material. FIG. 12 shows a spacer 120 that includes at least aportion of porous polymer material. FIG. 13 shows a spacer 130 thatincludes at least a portion of porous polymer material. FIG. 14 shows aspacer 140 that includes at least a portion of porous polymer material.FIG. 15 shows a spacer 150 that includes at least a portion of porouspolymer material. FIG. 16 shows a spacer 160 that includes at least aportion of porous polymer material. FIG. 17 shows a spacer 170 thatincludes at least a portion of porous polymer material.

FIG. 18 shows a multi-component spacer 180 that includes at least aportion of porous polymer material. A first portion 182, a secondportion 184, and a third portion 186 are shown attached together. In theembodiment shown, the portions are attached using a mechanicalattachment 188. In one example, the mechanical attachment includes adovetail configuration as shown in the figure. Although a dovetail is aneasy and effective mechanical attachment, the invention is not solimited. Other geometries of mechanical attachments 188 are within thescope of the invention.

FIG. 19 shows a spacer 190 that includes at least a portion of porouspolymer material. FIG. 20 shows a spacer 200 that includes at least aportion of porous polymer material. FIG. 21 shows a spacer 210 thatincludes at least a portion of porous polymer material. FIG. 22 shows aspacer 220 that includes at least a portion of porous polymer material.

FIG. 23 shows a multi-component spacer 230 that includes at least aportion of porous polymer material. A first portion 234, and a secondportion 236 are shown attached together using a mechanical attachment236. Similar to spacer 180 described above, in one example themechanical attachment 236 includes a dovetail arrangement or similarmechanical attachment.

Additional Surface Preparation

Embodiments described in the present disclosure can also include variousfinishing processes depending on desired final properties. Oneadditional surface treatment includes using a plasma treatment withionized oxygen or other gas. In selected embodiments, such a plasmatreatment alters surface chemistry in a to increase wettability. Anothersurface treatment includes a Hydroxylapatite (HA) coating to increase anosteoconductive potential of the implant surface. Another surfacetreatment includes a Calcium Phosphate Coating to increase theosteoconductive potential of the implant surface. Another surfacetreatment includes a titanium nitride coating to provide a surfacedesirable for bony ongrowth. Other surface treatments to provide asurface desirable for bony ongrowth include titanium or otherbiocompatible metal or oxide coatings applied by any of a number ofprocesses such as physical vapor deposition, chemical vapor deposition,etc.

Alternate Design Embodiments

Additional embodiments include an incorporation of larger, discreteβ-TCP, titanium or other osteoconductive particles to the coating powdermix. These larger osteoconductive particles are of approximately thesame size as the thermoplastic material. In selected embodiments, thediscrete osteoconductive particles enhance the osteoconductionproperties of the porous material already coated with β-TCP powder. Onesource of osteoconductive particles include CronOS™ manufactured bySynthes.

Alternate Applications

As noted above, other uses for the porous material include scaffolds fortissue ingrowth applications other than spinal spacers. The porousmaterial as described in embodiments above is further usable as a bonevoid filler in a number of applications where bone ingrowth is desiredin anatomical locations under physiological mechanical stresses. Anexample of an application other than a spinal spacer includesmanufacturing at least part of an implant suitable for use in cranial orcraniofacial defect repair.

For applications other than those described in spinal spacer examplesabove, it may be desirable to modify mechanical properties of the porouspolymer such as modulus, shear strength, etc. Changing the polymerand/or coating powder results in different mechanical properties asdesired. In selected embodiments, porous polymer structure propertiesare modified such that they are suitable for soft tissue ingrowth.

Alternate Materials/Coatings

The main bodies, or portions thereof, of some of the spacer embodimentsof the present invention are formed from PEEK polymer or other polymers.In addition to various polymer choices, coating powder materials can beselected that are other than β-TCP. Alternative powders such as BariumSulfate (BaSO4) or Strontium Carbonate (SrCO3) have similar effects onthe polymers during heating above the melt point as β-TCP.

Mechanical Testing

In reference to FIGS. 24 and 25A-25B, porous PEEK spacers were createdby placing the PEEK/β-TCP powder described above into a mold. The amountof powder mixture placed inside the mold determined the porosity of thefinal structure. The particle size range determined the pore size. Twotypes of samples with varying surface areas and heights were made toform spacers similar in geometry to those known in the industry. Thefinal samples were tested for compressive strength. FIG. 26 illustratesa graph showing the relationship between the compressive strength andthe porosity of the spacer of FIG. 24 , while FIG. 27 illustrates agraph showing the relationship between the compressive strength of thespacer of FIG. 25A-25B, having a 40 percent porosity, and the height ofthe spacer.

In reference to FIGS. 28A-28B, composite samples, as opposed to thefully porous samples, were made in which a solid PEEK cylinder wassandwiched between two porous PEEK endcaps. The solid core gives thecomposite it's higher compressive strength and the porous endcaps allowbone ingrowth from top and bottom vertebrae. FIG. 29 is a graph showingthe differences between the compressive moduli (stiffnesses) of a spacerformed entirely from porous PEEK, a spacer formed from solid PEEK spacerand having porous PEEK endplates (such as the spacer illustrated inFIGS. 28A-28B), a spacer formed entirely from solid PEEK, and a spacerformed entirely from cancellous bone. FIG. 30 illustrates a graphshowing the ultimate compressive strengths of a spacer formed entirelyfrom porous PEEK, a spacer formed from solid PEEK and having porous PEEKendplates (such as the spacer illustrated in FIGS. 28A 28B), and aspacer formed entirely from solid PEEK.

While a number of embodiments of the invention are described, the aboveexamples are not intended to be exhaustive. The foregoing description ofthe specific embodiments of the present invention have been described indetail for purposes of illustration. In view of the descriptions andillustrations, others skilled in the art can, by applying, currentknowledge, readily modify and/or adapt the present invention for variousapplications without departing from the basic concept of the presentinvention; and thus, such modifications and/or adaptations are intendedto be within the meaning and scope of the appended claims.

What is claimed is:
 1. An orthopedic implant comprising: a compositebody comprising a plurality of thermoplastic polymers, the compositebody including a first porous portion and a second solid portion bondedto the first porous portion; wherein the first porous portion comprisesa first thermoplastic polymer of the plurality of thermoplastic polymersthat comprises a PEAK family polymer and the second solid portioncomprises a second thermoplastic polymer of the plurality ofthermoplastic polymers that comprises polyethylene; and, wherein thefirst porous portion comprises a network of granules of the firstthermoplastic polymer bonded together a contact points and defining aplurality of interstitial spaces between the network of granules.
 2. Theorthopedic implant of claim 1, wherein the second thermoplastic polymerfurther comprises PAEK family, PCL, PLA, PGA, polyphenylene,polyphenylsulphone, polysulphone, PET, polyurethane, or combinationsthereof.
 3. The orthopedic implant of claim 1, wherein the PEAK familypolymer is PEEK or carbon reinforced PEEK.
 4. The orthopedic implant ofclaim 1, wherein the network of granules are melt-bonded together at thecontact points.
 5. The orthopedic implant of claim 1, wherein theinterstitial spaces have a pore size in the range 5 μm to 5000 μm. 6.The orthopedic implant of claim 1, wherein the granules have an averagesize in the range of about 0.25 mm to about 1.0 mm.
 7. The orthopedicimplant of claim 1, wherein the first porous portion has an averageporosity of between about 30% to about 45%.
 8. The orthopedic implant ofclaim 1, wherein the first thermoplastic polymer further comprises PAEKfamily, PCL, PLA, PGA, polyphenylene, polyphenylsulphone, polysulphone,PET, polyethylene, polyurethane, or combinations thereof.
 9. Theorthopedic implant of claim 8, wherein the first thermoplastic polymerfurther comprises PAEK family polymer.
 10. The orthopedic implant ofclaim 9, wherein the PAEK family polymer is PEEK, carbon reinforcedPEEK, PEKK, PEK, or PEKEKK, or combinations thereof.
 11. The orthopedicimplant of claim 10, wherein the PAEK family polymer is PEEK or carbonreinforced PEEK.
 12. The orthopedic implant of claim 1, wherein thesecond solid portion is configured in the shape of a solid core, a solidband, or a solid skin.
 13. The orthopedic implant of claim 12, whereinthe second solid portion is configured in the shape of a solid skin. 14.The orthopedic implant of claim 1, wherein each granule of the networkof granules defines a polymer granule surface, and wherein each polymergranule surface defines a microporous surface porosity comprising aplurality of micropores.
 15. The orthopedic implant of claim 14, whereinthe microporous surface porosity is in the range of about 0.1 μm toabout 100 μm.
 16. The orthopedic implant of claim 14, wherein thepolymer granule surface further comprises a coating powder on at least aportion of the polymer granule surface.
 17. The orthopedic implant ofclaim 16, wherein the coating powder comprises coating powder particleshaving a size in the range of 0.1 microns to 100 microns.